JP7311519B2 - Multiple illumination transmission over optical fiber - Google Patents

Description

This application is based on U.S. Provisional Patent Application No. 62/613,813, entitled "MULTIPLE ILLUMINATION TRANSMISSION THROUGH OPTICAL FIBER," filed Jan. 5, 2018, inventor Mark Harrison Farley. ) claiming the priority benefit of This provisional patent application is hereby incorporated by reference in its entirety as if fully and fully set forth herein.

TECHNICAL FIELD This disclosure relates to systems and devices for use in medical procedures and, more particularly, to systems and devices capable of transmitting illumination.

Microsurgical instruments are typically used by surgeons for a variety of procedures. For example, in ophthalmic surgery, microsurgical instruments may be used to remove tissue from delicate and confined spaces. Microsurgical instruments can be used, for example, in procedures for removal of the vitreous, blood, scar tissue, or the lens. Such instruments may include control consoles and surgical handpieces through which the surgeon cuts and removes tissue. For posterior segment surgery, the handpiece may be a vitreous cutter probe, a laser probe, an illumination probe, and/or an ultrasonic fragmentation device for cutting or fragmenting tissue. The handpiece may be used to supply long pneumatic (pneumatic) lines and/or power cables, optical cables, or infusion fluids to the surgical site and to withdraw or aspirate fluids and severed/fragmented tissue from the surgical site. It can be connected to the control console by flexible tubing. The cut, inject, and aspirate functions of the handpiece power the surgical handpiece (e.g., a reciprocating or rotating cutting blade, or an ultrasonic vibrating needle), also control the flow of infusion fluid, and It can be controlled by a remote control console that provides a vacuum source (compared to atmospheric air) for aspiration of the tissue that has been treated. The functions of the console can be manually controlled by the surgeon, usually by means of foot-operated switches or proportional controls.

Microsurgical instruments may also be used during vitreoretinal surgery, which is typically performed in the posterior chamber of the human eye, to treat various conditions at the back of the eye. In particular, vitreoretinal surgery is used to treat age-related macular degeneration (AMD), diabetic retinopathy and diabetic vitreous hemorrhage, macular holes, retinal detachment, epiretinal membranes, cytomegalovirus (CMV) retinitis, and Conditions such as many other ocular conditions may be treated.

Various configurations of prior art illuminated laser probes have been developed that utilize separate optical fibers for each light source and/or separate optical fibers for coherent laser delivery. Some prior art surgical procedures use a first optical fiber for delivery of non-coherent light for illumination and a first optical fiber for delivery of coherent laser beam light for surgical treatment of tissue. A separate second optical fiber is used. In such a probe configuration, groups of illumination fibers are arranged side-by-side inside a common needle lumen. However, this prior art technique requires a larger incision, or multiple incisions, to introduce multiple illumination sources and laser treatment light into the eye or other structure, thereby resulting in greater trauma to the surgical site. . Therefore, it is desirable to improve existing probes.

One or more embodiments of the present disclosure may include a probe for treating an eye of a patient. A probe may include a body and a tubular element, such as a needle, having a main lumen extending from the body. The probe can further include a visualization optical fiber within the main lumen, the visualization optical fiber adapted to emit illumination provided by at least one of a plurality of light sources operable therewith.

One or more embodiments of the present disclosure may include a probe system including a probe including a body and a tubular element having a main lumen extending from the body. A tubular element may include a distal end. The probe may further include a single visualization optical fiber within the main lumen. A single visualization optical fiber may be adapted to emit illumination from the distal end of the tubular element, the illumination provided by one of a plurality of light sources connected to the visualization optical fiber. The probe system may further include an optical switching system operable with multiple light sources. The optical switching system may be adapted to independently control each of the multiple light sources.

One or more embodiments of the present disclosure may include an illumination method that includes coupling each of multiple light sources to a single visualization optical fiber. The illumination method may further include inserting a probe into the patient's eye, the probe including a body and a tubular element having a main lumen extending from the body. The tubular element may include a distal end that is inserted into the patient's eye. A single visualization optical fiber may be disposed within the main lumen. The illumination method may further include emitting illumination provided by one of a plurality of light sources connected to a single visualization optical fiber. An optical switching system operable with multiple light sources may allow switching between each of the multiple light sources.

Non-limiting embodiments of the present disclosure are described by way of example with reference to the accompanying drawings, which are schematic and not intended to be drawn to scale. In the figures, each identical or nearly identical component illustrated is typically represented by a single numeral. For clarity, not all components are labeled in all figures and examples of each embodiment are shown where illustration is not necessary to enable those skilled in the art to understand the present disclosure. Not all components are shown.

1 shows a perspective view of an exemplary surgical system according to aspects of the present disclosure; FIG. FIG. 2 shows a perspective view of an exemplary probe according to aspects of the present disclosure; FIG. 3 is a cross-sectional view of an exemplary probe in use on a patient, according to aspects of the present disclosure; FIG. 4 is a block diagram of a probe system according to aspects of the present disclosure; FIG. 5 is a stylized diagram showing a portion of the probe of FIG. 2, in accordance with aspects of the present disclosure; 6A is a side cross-sectional view of a portion of the probe of FIG. 2, according to aspects of the present disclosure; FIG. 6B is a side cross-sectional view of a portion of the probe of FIG. 2, according to aspects of the present disclosure; FIG. FIG. 7 is a block diagram illustrating an optical switching system according to aspects of the present disclosure; FIG. 8 is a flowchart illustrating an illustrative method for providing single-fiber illumination according to aspects of the present disclosure;

The accompanying drawings can be better understood with reference to the following detailed description.

For the purposes of promoting an understanding of the principles of the disclosure, reference will now be made to the implementations illustrated in the drawings and specific language will be used to describe the same. It will nevertheless be understood that no limitation of the scope of the disclosure is intended unless specifically indicated. All changes and further modifications to the described devices, instruments, methods, and all further applications of the principles of this disclosure are fully contemplated as would normally occur to one skilled in the art to which this disclosure pertains. In particular, it is fully contemplated that features, components and/or steps described with respect to one implementation may be combined with features, components and/or steps described with respect to other implementations of the disclosure. be done. For simplicity, in some instances the same reference numbers are used throughout the drawings to refer to the same or like parts.

Ophthalmic surgical illuminators for use with fiber optics have been manufactured by many companies over the years. One such device is Alcon Research Ltd. (6201 South Freeway, Fort Worth, TX, 76134). The present disclosure improves on existing devices by allowing multiple illumination characteristics to be delivered through a single visualization/illumination optical fiber during ophthalmic surgery. Unlike prior art systems that use one or more dedicated optical fibers to support each different optical function or property, the embodiments herein employ different intensity and wavelength narrowbands with independent modulation. Advantageously, it allows the combination of angular and wide-angle beams within the same optical fiber. By allowing multiple light sources to share the same optical fiber, the diameter of the needle can be reduced, thus minimizing trauma to the surgical site. Independent modulation of each multiplexed light source using methods appropriate for each light source or combination of light sources, such as time-length division multiplexing, wavelength division multiplexing, current/voltage control, polarization control, and/or optical attenuation. can be achieved.

As described in more detail herein, embodiments of the present disclosure provide for time division multiplexing between different surgical light sources for quasi-simultaneous delivery over the same optical path, such as an optical fiber within a surgical instrument. to achieve Light sources can be alternated using micro-electro-mechanical systems (MEMS) or other fast switching or modulation means. Switching frequencies that exceed video and human refresh rates can simulate simultaneous lighting from multiple sources with different functions or characteristics. In the methods described herein, multiple light sources can be combined via one or more multiplexed optical switches to provide various lighting characteristics, e.g., different colors, intensities, divergence angles. , these properties may be independently adjustable to provide visualization and illumination of various tissues or media during ophthalmic surgery, for example.

To date, multiple illumination characteristics have not been commonly used during ophthalmic surgery. New applications such as visualization of the vitreous have demonstrated the value of combining narrow-angle and wide-angle beams with different intensities and wavelengths with independent modulation. Accordingly, embodiments herein provide an advantageous solution for visualization of the vitreous.

The present disclosure is directed broadly to systems and instruments for treating an eye of a patient. In one or more embodiments, a probe includes a body and a tubular element such as a needle having a main lumen extending therefrom, the tubular element including a distal end. The probe further includes a visualization optical fiber within the main lumen, the visualization optical fiber adapted to emit illumination provided by at least one of the plurality of light sources connected to the visualization optical fiber. In some embodiments, the probe further includes an optical switching system (e.g., time division multiplexer) operable with multiple light sources, wherein the optical switching system independently controls each of the multiple light sources. be adapted. By providing time division multiplexing between different surgical light sources, quasi-simultaneous illumination delivery via the same optical path can be achieved.

FIG. 1 illustrates an exemplary surgical console (referred to interchangeably as “console”) 10 within the scope of this disclosure. Surgical consoles are available from Alcon Laboratories, Inc. (6201 South Freeway, Fort Worth, Tex., 76134) vitreoretinal surgical console, such as the Constellation® surgical console. As shown, console 10 may include one or more ports 20, which may be utilized to provide injection and/or irrigation fluids to the eye or to aspirate substances from the eye. Console 10 may also include display 30 for interfacing with console 10 , such as for establishing or modifying one or more operations of console 10 . In some examples, display 30 may include a touch-sensitive screen for interacting with console 10 by touching the screen of display 30 . A probe, such as a vitrectomy probe that includes illumination fibers connected to multiple light sources, may be coupled to port 20 for dissecting ocular tissue and aspirating ocular tissue from the eye.

FIG. 2 shows an exemplary vitrectomy probe 40 (hereinafter "probe"). Probe 40 includes a body 45 and a tubular element in the form of needle 50 extending from body 45 . As shown in FIG. 3, during ophthalmic surgery, such as retinal surgery, needle 50 is inserted into posterior portion 60 of eye 70, such as through cannula 80 placed in incision 90 through sclera 100 of eye 70. to illuminate, remove, and/or aspirate ocular tissue. For example, during retinal surgery, needle 50 may be inserted into posterior portion 60 of eye 70 and one or more light sources may be used to illuminate the surgical site within eye 70 . In some embodiments, the needle 50 has a vitreous humor (referred to interchangeably herein as “vitreous” or “vitreous material”) 110 , a jelly-like substance that occupies the volume defined by the posterior portion 60 . may further include a cutter (eg, mechanical or laser) to remove the . The needle 50 may also be used to remove membranes covering the retina or other tissue.

FIG. 4 is a schematic diagram of exemplary components of vitrectomy probe system 105 . Vitrectomy probe system 105 may include vitrectomy probe 40 , pneumatic source 120 , probe driver shown as adjustable directional on-off pneumatic driver 122 , muffler 124 , and controller 126 . In one embodiment, controller 126 may be a processor including one or more processing cores capable of performing parallel or sequential operations. Alternatively, controller 126 may be dedicated hardware such as an application specific integrated circuit (ASIC), to name just a few examples. Air pressure source 120, driver 122, muffler 124, and probe 40 are in fluid communication with each other along lines representing flow paths or flow lines. Controller 126 is in electrical communication with driver 122 . In one embodiment, controller 126 controls the operation of both driver 122 and various aspects of probe 40 . The vitrectomy probe system 105 can further include an optical switching system 130 operable with multiple light sources 150, as described in more detail below.

Although not shown for the sake of brevity, vitrectomy probe system 105 may include multiple subsystems that are used together to perform eye surgery, such as emulsification or vitrectomy surgery. The vitrectomy probe system 105 may include one or more types of memory such as RAM (random access memory), ROM (read only memory), flash memory, disk-based hard drives, and/or solid state hard drives. It may include information or data storage systems. The controller 126 and data storage system can communicate via a bus, which also enables communication with and between one or more of the multiple subsystems of the vitrectomy probe system 105. can be

FIG. 5 shows a portion of an illustrative vitrectomy probe 40 operable with multiple light sources 150 . According to some embodiments, vitrectomy probe 40 includes multiple light sources 150 connected to a handle or body 45 containing visualization optical fibers 155 that terminate in needle 50 . A visualization optical fiber 155 can transmit light from one of a plurality of light sources 150A-C, which can be, for example, internal illumination for visualization, optical coherence tomography (OCT) imaging, and/or For example, biometrics for visualization and diagnosis can be provided using various lighting characteristics. In one non-limiting embodiment, first light source 150A can be a narrow angle beam connected to visualization optical fiber 155 via connector 157, and second light source 150B can be a visualization light beam via connector 158. A third light source 150C can be a colored (eg, blue or red) light connected to visualization optical fiber 155 via connector 159, which can be a wide angle beam coupled to fiber 155. FIG. In various embodiments, each of the plurality of light sources 150 can have different intensities (eg, different wavelengths). It will be appreciated that greater or lesser numbers of light sources may be possible within the scope of this disclosure.

Each of connectors 157 , 158 , and 159 can be an optical fiber optically coupled to a single visualization optical fiber 155 within or before reaching body 45 of probe 40 . For example, the optical coupling may be free space optics, optical couplers, fused fiber couplers, wavelength division multiplexers, time division multiplexers, frequency division multiplexers, or alternating each of the multiple light sources 150A-C. can be achieved through the use of one or more optical switches, or a combination thereof. In an exemplary embodiment, the output of each of the light sources 150A-C can be switched using MEMS or other fast switching or modulation means that alternates between multiple light sources 150A-C. A switching frequency that exceeds the refresh rate of video and the human eye can be selected to simulate simultaneous lighting with multiple light sources 150A-C, each with different functions and/or characteristics.

In some embodiments, body 45 forms a handle portion that can be grasped and manipulated by a surgeon when performing a surgical procedure such as a vitrectomy. Body 45 may be made from a variety of materials commonly used to form such tools. For example, body 45 may be made of lightweight aluminum, polymer, or other material. In various embodiments, body 45 may be sterile and used in more than one surgical procedure, or may be a disposable device. The inner portion of body 45 is designed to accommodate visualization optical fiber 155 . In the illustrated embodiment, the plurality of light sources 150 are positioned outside the body 45 . In other embodiments, one or more of the plurality of light sources 150 may be positioned inside body 45 . Additionally, body 45 may house one or more switching components (eg, MEMS or frequency division multiplexers). In other embodiments, the switching components may be located remotely from body 45 .

In various embodiments, probe 40 includes multiple light sources 150 (e.g., halogen, mercury vapor, xenon narrow band or broad spectrum bulbs, broadband, supercontinuum or narrowband lasers, LED superluminescent diodes, laser diodes, or other It includes an internal illumination probe that includes a visualization optical fiber 155 (eg, a single-mode or multimode optical fiber) connected to a solid-state or semiconductor light-emitting device). Light provided by each of the plurality of light sources 150A-C travels through visualization optical fiber 155 and illuminates an area of interest. Depending on the particular application, the free end or distal tip of visualization optical fiber 155 may be terminated in any of a variety of ways. For example, the tip of the visualization optical fiber 155 may simply be polished and/or angled to provide a particular illumination area and angle, or one or more polarizers, for example to focus or diverge the light. may be coupled to the lens of In an alternative configuration, a lens is incorporated into visualization optical fiber 155 via a gradient index, where the refractive index of the fiber itself varies gradually over the longitudinal axis of visualization optical fiber 155 to direct the convergence or divergence of propagating light. offer. By using a lens to disperse the light, a smaller diameter fiber can be used to achieve a similar illuminated area (spot size) at a given working distance, which is equivalent to a single visible light It is particularly useful in multi- or single-function probes where fibers are used.

6A-B, needle 50 of probe 40 (FIG. 5) according to an embodiment of the present disclosure will now be described in greater detail. Figures 6A-B show two different non-limiting fiber and lens configurations according to various embodiments of the present disclosure. In the configuration shown in FIG. 6A, probe tip 160 features needle 50 including visualization optical fiber 155 and treatment fiber 161 . Visualization optical fiber 155 can be a multimode fiber for propagating the internal illumination light to the distal end of probe tip 160 . In some embodiments, treatment fiber 161 can be an optical treatment fiber such as a surgical laser fiber for projecting a laser beam from probe tip 160 . The end of visualization optical fiber 155 is optionally retracted from the end of probe tip 160 to allow wider dispersion from visualization optical fiber 155, resulting in a larger illumination spot for internal illumination. diameter is produced. In some embodiments, the spot size is adjustable by using a slide lever 162 mechanically coupled to visualization optical fiber 155 . Movement of slide lever 162 along the longitudinal axis of needle 50 adjusts the distance between the end of visualization optical fiber 155 and the end of probe tip 160, resulting in different illumination spot sizes.

The configuration shown in FIG. 6B is similar to that of FIG. 6A except that both visualization optical fiber 155 and treatment fiber 161 are housed within inner needle 164 . In this example, visualization optical fiber 155 is fixedly mounted within inner needle 164 such that visualization optical fiber 155 moves with inner needle 164 when sliding lever 162 is repositioned. Treatment fiber 161 can be threaded through inner needle 164, but is attached to needle 50 so that it does not move when slide lever 162 is moved.

In some embodiments, treatment fiber 161 may be designed to act as an optical waveguide and propagate a laser beam. In some examples, the properties of the laser beam propagated through treatment fiber 161 are such that the laser beam causes disruption of vitreous fibrils in the path of the laser beam. In some embodiments, the laser may have a pulse rate within the range of approximately 10-500 kilohertz (kHz). This range can effectively provide destruction, which is the mechanical effect of light on tissue to destroy or degrade tissue by rapid ionization of molecules by the laser. Other ranges of characteristics of the laser beam that can cause destruction are also conceivable.

In some examples, probe 40 includes an aspiration lumen for aspirating severed vitreous tissue and other vitreous fluid. The aspiration lumen may be connected with an aspiration mechanism that provides a vacuum force to withdraw severed tissue and other fluids. In some instances, main lumen 165 of needle 50 serves as part of the aspiration lumen, as shown. However, in some instances, a separate independent cannula with an aspiration lumen is positioned within main lumen 165 . Such an aspiration lumen is connected with a needle port so that severed tissue properly enters the aspiration lumen.

7, the operation of optical switching system 130 according to some embodiments of the present disclosure will now be described in greater detail. As shown, optical switching system 130 includes an output 168 coupled to each of a plurality of light sources 150A-C and directed to visualization optical fiber 155. FIG. In some embodiments, the optical switching system 130 can emit different wavelengths, e.g., in the red, green, and blue ranges, e.g., different luminous intensities, e.g., measured in candela, and/or different divergences, e.g., narrow-angle or wide-angle beams. It operates by selectively alternating the light output of a plurality of constituent lasers having .

Optical switching system 130 may be an optical combiner such as a time division multiplexer. Time division multiplexing can be used to transmit and route signals in optical communication networks. In one example, time-division multiplexing involves dividing a frame or time slot into multiple equally spaced time slots and removing more It involves synchronously inserting a single bit of data into a high bandwidth multiplexed stream. Signal recovery may include a demultiplexing operation in which the high bandwidth stream is split into individual low bandwidth sources. The inherent simplicity of electronic time division multiplexing gives the processing logic and devices required to be simpler to implement than simple and complex protocols.

In the embodiment shown in FIG. 7, time division multiplexed optical switching system 130 may include three input signal optical fibers that transmit pulses to a corresponding array of optical switches 170A-C. An input pulse on the input fiber can be placed in each corresponding time division multiplexed slot. In some embodiments, the multiplexing can be time dithered to avoid time aliasing effects due to switching illumination when viewed through an optical or digital display system. Additionally, multiplexing can serve as an efficient and reliable means of modulation and/or attenuation, potentially helping to reduce light exposure or phototoxic damage to tissue.

In some embodiments, time division multiplexed optical switching system 130 may include optical shutter 172 to allow optical signals to be time division multiplexed. In the illustrated example, the optical shutter 172 is a rotatable wheel or disk, a digital light processing (DLP) device, a MEMS device, a rotating polygon mirror, a cascaded tunable optical filter or modulator, a liquid crystal diode shutter, and/or Other suitable optical shutters may be used. In some examples, multiple light sources 150A-C may be controlled (eg, periodically turned on and off) to transmit optical signals in different time slots and/or at different frequencies, intensities, divergences, etc. can be switched).

In other embodiments, optical switching system 130 may be an optical time division multiplexer (“OTDM”). Some OTDMs include fiber loops that include nonlinear optical elements positioned asymmetrically within the loop. The OTDM functions as an optical AND gate that allows optical pulses to pass through when in the proper time slot. OTDM operates by first splitting the input signal pulse into two beams. These beams are coupled into a fiber optic loop but travel in opposite directions around the loop. The optical control pulses are timed to change the refractive index of the nonlinear optical element, thus creating a phase difference between the counter-propagating optical signal pulses. As the optical signal pulses pass through the fiber loop, they are combined together. If the pulses are in phase, constructive interference will occur and the pulses can exit the OTDM. However, when the optical pulses are out of phase, destructive interference occurs and the optical signal cannot pass.

In an exemplary embodiment, optical switching system 130 combines light from three light sources 150A-C into a single fiber-coupled output 168 suitable for interfacing to probe 40 using single mode fiber. . The optical switching system 130 independently controls each of the plurality of light sources 150A-C to, for example, adjust the video refresh rate (eg, 120, 240, or 300 frames/second) and the human eye refresh rate (eg, Each of the plurality of light sources 150A-C is configured to activate and deactivate according to a random switching frequency higher than approximately 50 Hz to 90 Hz to reduce synchronization artifacts or interference with other equipment.

The intensity of each wavelength of the multiple light sources alters their respective contributions to the internal illumination light output, e.g., to provide different therapeutic effects, to provide improved visualization, or to prevent tissue damage. may be changed for This may allow the surgeon to see the tissue under different hues of white light, which can help highlight specific features, such as contrasting specific structures (e.g. blood vessels) or blotches. and/or fluoresce the blemishes (eg, ophthalmic use of indocyanine green or triptan blue). The intensity of the contributing wavelengths can be adjusted, for example, to comply with safety guidelines such as those recommended by the International Committee on Non-Ionizing Radiation Protection to prevent photochemical retinal damage. In one non-limiting embodiment, the intensity of the blue contribution can be reduced to limit the blue spectrum light from the white light laser source. For example, light having wavelengths less than about 475 nm may be excluded from the output of a white light laser system to protect against phototoxicity. Such selected wavelengths can also be filtered out using an external filter coupled to the white light laser source or probe.

FIG. 8 illustrates a method 200 of treating a patient using a probe. As shown, at block 202, method 200 may include coupling each of a plurality of light sources to a single visualization optical fiber of the probe. In some embodiments, each of the multiple light sources includes different lighting characteristics such as color, wavelength, intensity, and/or divergence.

At block 204, method 200 may include inserting a probe into the patient's eye. In some embodiments, the probe is a vitrectomy probe. In some embodiments, the probe has a body and a tubular element having a main lumen extending from the body, the tubular element including a distal end for insertion into the patient's eye. The probe may further include a single visualization optical fiber within the main lumen.

At block 206, method 200 can include emitting illumination provided by one of a plurality of light sources connected to a single visualization optical fiber, wherein an optical switching system operable with multiple light sources is , allowing switching between each of a plurality of light sources. In some embodiments, the method 200 can include switching between each of multiple light sources using a time division multiplexer. In some embodiments, each of the plurality of light sources may each be activated or deactivated using a random switching frequency, the random switching frequency being perceived by two or more of the plurality of light sources. exceed the prescribed video refresh rate to provide simultaneous illumination. However, in use, only one of the multiple light sources is activated at a time to provide illumination for a single visualization optical fiber.

Embodiments herein provide one or more of the following technical benefits/advantages. First, by allowing multiple light sources to share the same optical fiber, the diameter of tubular elements (e.g., needles) can be reduced, thus minimizing trauma to the surgical site. be able to. Second, time-division multiplexing between different surgical light sources can achieve quasi-simultaneous light delivery via the same optical path, even though only a single light source can be switched on at any given time. . Third, switching frequencies exceeding video and human refresh rates can simulate simultaneous lighting with multiple light sources while mitigating synchronization artifacts or interference with other equipment.

Some embodiments may be described using the terms "proximal" and "distal" when used in connection with a vitrectomy probe. As used herein, "proximal" refers to the end of the probe closest to the surgeon, while "distal" refers to the end of the probe inserted into the patient. Further, as used herein, the singular forms "a," "an," and "the" are intended to include plural forms as well, unless the context clearly indicates otherwise. As used herein, the terms “comprises” and/or “comprising” or “includes” and/or “including” refer to the features, regions, steps, or , elements and/or components, but does not preclude the presence or addition of one or more other features, regions, integers, steps, operations, elements, components and/or groups thereof will be further understood.

Although specific embodiments have been illustrated and described herein, it is to be understood that any configuration calculated to accomplish the same purpose may be used in place of the specific embodiments shown. This disclosure is intended to cover any and all adaptations or variations of various embodiments. It should be understood that the above description has been made in an illustrative manner and is not restrictive. Combinations of the above embodiments, and other embodiments not specifically described herein, will be apparent to those of skill in the art upon reviewing the above description. Accordingly, the scope of various embodiments includes any other applications in which the compositions, structures, and methods described above are used.

While the subject matter has been described in language specific to structural features and/or methodological acts, it is understood that the subject matter defined in the appended claims is not necessarily limited to the specific features and acts described above. want to be Rather, the specific features and acts described above are disclosed as example forms of implementing the claims.

Claims (14)

A vitrectomy probe system comprising:
body,
a tubular element having a main lumen extending from said body ;
a plurality of light sources connected to the body and comprising a first light source having a narrow beam and a second light source having a wide beam;
an optical switching system operable with the plurality of light sources, the optical switching system configured to switch the plurality of light sources at a switching frequency ; and
a visualization optical fiber within the main lumen, the visualization optical fiber configured to emit, via the optical switching system , illumination provided by the plurality of light sources operable with the visualization optical fiber;
with
A vitrectomy probe system wherein the switching frequency for switching between the multiple light sources is higher than the refresh rate of the human eye and the multiple light sources through the visualization optical fiber exhibit the appearance of simultaneous lighting. 3. The vitrectomy probe system of Claim 1, wherein the optical switching system independently controls each of the plurality of light sources. 3. The vitrectomy probe system of claim 1 , wherein said optical switching system is a time division multiplexer. 4. The vitrectomy probe system of claim 3 , wherein the time division multiplexer includes one or more microelectromechanical systems for switching between each of the plurality of light sources. The vitrectomy probe system of Claim 1 , wherein the optical switching system activates or deactivates each of the plurality of light sources according to a random switching frequency. 6. The vitrectomy probe system of claim 5 , wherein said random switching frequency exceeds a predetermined video refresh rate. 3. The vitrectomy probe system of claim 1, wherein each of said plurality of light sources comprises different illumination characteristics. 8. The vitrectomy probe system of claim 7 , wherein the illumination feature comprises at least one of wavelength, intensity and divergence. 3. The vitrectomy probe system of claim 1, further comprising an optical treatment fiber within said main lumen, said optical treatment fiber projecting a laser beam. A vitrectomy probe system comprising:
a vitrectomy probe , the vitrectomy probe comprising :
body,
a tubular element having a main lumen extending from said body and having a distal end ;
a plurality of light sources connected to the body and comprising a first light source having a narrow beam and a second light source having a wide beam;
a single visualization optical fiber within the main lumen configured to emit illumination provided by a plurality of light sources connected to the single visualization optical fiber from the distal end of the tubular element; a single visualization optical fiber, and
an optical switching system operable with the plurality of light sources, the optical switching system configured to independently control each of the plurality of light sources and configured to switch the plurality of light sources at a switching frequency ;
has
A vitrectomy probe system wherein the switching frequency for switching between the multiple light sources is higher than the refresh rate of the human eye and the multiple light sources through the visualization optical fiber exhibit the appearance of simultaneous lighting. 11. The vitrectomy probe system of Claim 10 , wherein said optical switching system is a time division multiplexer. 12. The vitrectomy probe system of claim 11 , wherein the time division multiplexer includes one or more microelectromechanical systems for switching between each of the plurality of light sources. 11. The vitrectomy probe system of Claim 10 , wherein the optical switching system activates or deactivates each of the plurality of light sources according to a random switching frequency. 11. The vitrectomy probe system of claim 10, wherein each of said plurality of light sources comprises a different illumination characteristic, said illumination characteristic comprising at least one of wavelength, intensity and divergence .

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